CN110575272B

CN110575272B - Implant material

Info

Publication number: CN110575272B
Application number: CN201810578198.XA
Authority: CN
Inventors: 苏国材; 苏昱荣
Original assignee: Taiwan Shan Yin International Co Ltd; BIOMATE MEDICAL DEVICES Tech CO Ltd
Current assignee: Taiwan Shan Yin International Co Ltd; BIOMATE MEDICAL DEVICES Tech CO Ltd
Priority date: 2018-06-07
Filing date: 2018-06-07
Publication date: 2021-05-25
Anticipated expiration: 2038-06-07
Also published as: CN110575272A

Abstract

The invention discloses an implant material, which comprises an implant body with a thread part, and a drill locking part and a locking hole which are respectively arranged at two ends of the implant body; when the implant material is applied to a locked part such as a bone part needing cell proliferation, bone cells derived in a healing process can be quickly attached to the end edges of the holes and extend into the channels to smoothly climb and proliferate, and the proliferated cells are further linked among the holes and the channels to stably coat the implant body for positioning, so that the combination effect between the implant body and the locked part is improved, and the healing time of the locked part is favorably shortened.

Description

Implant material

Technical Field

The present invention relates to an implant, and more particularly to an implant that can promote cell proliferation and healing.

Background

The application of the implant material is very wide, especially common in the application fields of dentistry and orthopaedics, and the following description only takes the application of dental implant in the dentistry field as an example, namely, the metal artificial implant is implanted into the alveolar bone of the oral cavity, which is the common medical action for the defect of teeth at present, after the implant is implanted into the alveolar bone, the bone integration effect can be achieved through the process of combining the bone cells derived from the alveolar bone and the implant; for the implant to be combined with the alveolar bone, a porous structure is used on the surface of the implant, so that bone cells can be attached to the porous structure to be combined with the implant, but the traditional pore formation is prone to have problems of different sizes, depths and intervals, which is not favorable for the combination operation between the bone cells initially derived from the alveolar bone and the implant, i.e., the scale of the initial cells may be too small, and when the cells grow to a degree greater than the size of the pores, the cells can extend outwards to form chains between the pores, but the osseointegration process takes a long time, so that the healing time of the bone tissue is long and needs to be improved.

Disclosure of Invention

Therefore, the present invention is directed to provide an implant material, which allows cells to rapidly and smoothly climb onto an implant, so as to promote the growth ability of the cells, achieve stable combination between the implant and a locked part, and shorten the healing time of the tissue at the locked part.

Therefore, the implant material comprises an implant body with a thread part, and a drill locking part and a locking hole which are respectively arranged at two ends of the implant body; the surface of the implant is provided with a plurality of holes, the surface of the implant at least comprises a rod body surface which is exposed outwards between any two adjacent screw threads of the screw thread part, each hole is provided with a peripheral wall, an end edge is formed at the joint of the peripheral wall and the surface of the implant, the end edges of the adjacent holes are connected to ensure that the adjacent peripheral walls are connected, so that the adjacent holes are communicated in succession to construct a channel, and the communication of the holes forms a plurality of series connection types so as to form a plurality of channels; according to the above, after the implant material is implanted into a locking position, the cells derived from the locking position can be easily attached to the end edges of the holes and extend into each channel of the holes for rapid attachment and proliferation, and the proliferated cells extend outwards from the holes and the channels and are continuously attached to other holes and channels, so as to form an inter-cell linking effect, so that the cells can stably attach to the implant in a short time to achieve the effect of coating and positioning the implant, thereby greatly improving the bonding effect between the implant and the locking position, avoiding the implant from loosening in the healing process and being more beneficial to shortening the healing time of tissues at the locking position.

Drawings

FIG. 1 is a schematic diagram of a first preferred embodiment of the present invention.

FIG. 2 is a schematic diagram of a second preferred embodiment of the present invention.

FIG. 3 is a schematic diagram of a third preferred embodiment of the present invention.

Fig. 4A to 4H are schematic diagrams of different embodiments of the hole distribution of the implant of the present invention, wherein fig. 4A and 4B are enlarged schematic diagrams at the encircled area of fig. 1, fig. 4C, 4D and 4G are enlarged schematic diagrams at the encircled area of fig. 2, and fig. 4E, 4F and 4H are enlarged schematic diagrams at the encircled area of fig. 3.

Fig. 5A to 5C are enlarged plan views illustrating the connection of implant holes to form channels of different communication patterns according to the present invention.

Fig. 6 is a perspective view of fig. 5A.

Fig. 7 to 9 are schematic views illustrating the use of the present invention in dental implant surgery.

Description of reference numerals:

3 implant material

31 implant 32 hole

311 drill locking part 312 locking hole

313

thread part

3131, 3132 thread segment

Peripheral wall 321 end edge

323 channel

E1, E2 first end, P1, P2 thread pitch

Maximum outer diameters of first and second ends of OD1 and OD2

5-alveolar bone 51 predrilled hole

BC cell S implant surface

S1 shaft surface S2 thread surface

Detailed Description

In order to make the objects, technical solutions and advantages of the embodiments of the present invention clearer, the technical solutions in the embodiments of the present invention will be clearly and completely described below with reference to the drawings in the embodiments of the present invention, and it is obvious that the described embodiments are some, but not all, embodiments of the present invention. All other embodiments, which can be obtained by a person skilled in the art without any inventive step based on the embodiments of the present invention, are within the scope of the present invention.

The implant 3 of the preferred embodiment of the present invention is mainly used in medical implantation, such as in the closure site requiring cell proliferation in dentistry, orthopedics, etc., that is, the implant 3 can be used as an artificial implant implanted into the alveolar bone in the oral cavity, or as an implant used in orthopedic surgery, such as an artificial bone screw, etc., and the following description will only take the closure site as the alveolar bone in the oral cavity, and the implant 3 is taken as an implant implanted into the alveolar bone as an example.

Referring to fig. 1, the implant 3 of the present invention includes an implant 31, a drill locking portion 311, and a locking hole 312 opposite to the drill locking portion 311; wherein the implant 31 has a first end E1 and a second end E2 opposite to the first end E1, the drill-locking portion 311 is disposed at the first end E1, the locking hole 312 is formed at the second end E2 of the implant 31 and opposite to the drill-locking portion 311, a thread portion 313 is spirally disposed between the two ends E1 and E2 on the implant 31, the thread portion 313 may include a thread section 3131 extending from the first end E1 to the second end E2, a pitch P1 is formed between any two adjacent threads of the thread section 3131 to form a one-step thread structure (see fig. 1); or the thread portion 313 includes at least two thread sections 3131, 3132 (see fig. 2, 3), which are only illustrated by way of example, that is, a thread section 3131 extending from the first end E1 of the implant 31 is spirally disposed on the implant 31, and another thread section 3132 extending from the thread section 3131 to the second end E2, a pitch P1 is formed between any two adjacent threads of the thread section 3131, a pitch P2 is formed between any two adjacent threads of the another thread section 3132, the pitch P1, P2 may be different, for example, the pitch P1 of the thread section 3131 is greater than the pitch P2 of the another thread section 3132, while the maximum outer diameter OD2 of the second end E2 may be equal to the maximum outer diameter 1 of the first end E1 (see fig. 3), or the maximum outer diameter E37 of the second end E2 may be greater than the maximum outer diameter E9634 of the second end E3631 (see fig. 3), so that the outer diameter of the other thread section 3132 is gradually increased toward the direction opposite to the drill locking portion 311, which is beneficial to the effect of fast and stable locking.

Furthermore, the surface S of the implant 31 is provided with a plurality of holes 32, the size and shape of the holes 32 are not limited, the surface S includes any surface of the implant 31 that can be exposed to the outside, for example, the implant surface S includes a shaft surface S1, the shaft surface S1 is an outer surface that extends axially from the first end E1 to the second end E2 and is exposed to the outside, and the outer surface can be exposed between any two adjacent threads of the thread part 313, or the implant surface S can include the shaft surface S1 and a thread surface S2 of all or part of the thread part 313, so that the partial area or all areas of the implant 31 exposed to the outside are provided with the holes 32: taking the first-stage thread structure of fig. 1 as an example, a hole 32 may be formed in the shaft body surface S1 exposed between adjacent threads of the thread section 3131 (as shown in fig. 4A), or a hole 32 may be formed in any of the thread surfaces S2 (such as the upper and lower thread surfaces or both thread surfaces) of the threads of the thread section 3131 and the shaft body surface S1, as shown in fig. 4B.

If the two-step thread structure shown in fig. 2 and 3 is taken as an example, a hole 32 may be formed on the shaft surface S1 exposed between any two adjacent threads of the two

thread segments

3131, 3132 as shown in fig. 4G and 4H; or as shown in fig. 4C and 4E, a hole 32 is formed on any thread surface S2 of the thread of the shaft surface S1 and a thread section 3131 thereof; or as shown in fig. 4D and 4F, holes 32 are formed on any of the thread surfaces S2 (e.g., upper and lower thread surfaces or both thread surfaces) of the threads of the shaft surface S1, the thread section 3131 and the other thread section 3132.

Referring to fig. 6, each of the holes 32 has a peripheral wall 321, the peripheral wall 321 extends from the surface S of the implant to the inside of the implant 31 to form the hole 32, the peripheral wall 321 is connected to the surface S of the implant at an end 322, the end 322 of any one of the holes 32 is connected to the end 322 of another adjacent hole 32 to connect the adjacent peripheral walls 321, so that the adjacent holes 32 are connected one by one to form a channel 323, the implant 32 is connected to the holes 32 to form a plurality of channels 323, which can be shown in fig. 5A to 5C (described later), where fig. 5A is shown in fig. 6 in a perspective view, and the holes 32 in fig. 4A to 4H are also shown in fig. 5A by way of example; furthermore, the edge 322 of each hole 32 can be non-flat, such as a non-smooth line with a concave-convex pattern formed at the edge where the peripheral wall 321 meets the surface S of the implant, so that the edge 322 is rough, as described below by taking the edge 322 as a rough example.

The connection of the holes 32 affects the communication direction of each channel 323, for example: the holes 32 are connected in series around the implant surface S (in the X direction) so that a plurality of independent transverse channels 323 are formed in the implant 31, which are shown as transverse communication spaces in fig. 5A and 6; the plurality of holes 32 may also be connected in the Y direction (e.g., axially) as shown in fig. 5B to form a plurality of independent longitudinal channels 323, which are longitudinally connected as shown in fig. 5B; the holes 32 can also be connected in the direction X, Y to connect the adjacent independent channels 323, thereby forming a criss-cross through pattern, which is shown in fig. 5C as a longitudinal and a transverse connecting space; the above-mentioned communication configurations allow the cells to form a uniform and regular distribution during the climbing and proliferation processes, and further link with each other to firmly wrap the implant 31 to position the implant 31, which is only illustrated in the form of fig. 5A.

Referring to fig. 7, in use, the implant 3 is applied to a tooth implantation operation in an alveolar bone 5 implanted in an oral cavity as an example; when the tooth implantation operation is performed, a surgical instrument (not shown) is inserted into the locking hole 312 to drive the screw part 313 to perform cutting attack on the wall surface of the pre-drilled hole 51 of the alveolar bone 5 so as to achieve implantation positioning; if the implant 31 has two thread segments 3131, 3132 (see fig. 8), the thread segment 3131 with a larger pitch P1 contacts the wall surface in a large area during the drilling process to cut and thread the wall surface into the pre-drilled hole 51, and then the other thread segment 3132 with a smaller pitch P2 continues to cut and thread along the spiral track of the thread segment 3131, so that the implant 31 can be quickly threaded into the alveolar bone 5 to reduce the discomfort of the patient during the operation process and achieve the stable positioning of the implant.

After the implant 31 is implanted into the alveolar bone 5, the alveolar bone 5 derives bone cells BC (only schematically shown in fig. 9) during the healing process, since the edges 322 of the holes 32 are rough, the bone cells BC can be rapidly and smoothly adhered to the edges 322 and extend into the holes 32, and then the adhesion and proliferation actions are performed inside and outside the holes 32, in other words, after the bone cells BC enter the holes 32 along the edges 322 and are implanted, the proliferated and differentiated cell proliferation actions can be rapidly adhered to and performed on the peripheral wall 322 of the channels 323, and through the internal communication space of each channel 323, the proliferated bone cells BC can be continuously adhered and extended along the peripheral wall 322 to extend into each channel 323, and then extend out from the respective channels 323, the holes 32 and attach to other channels, holes 32 along the surface S323, further, the bone cells BC can be tightly linked with each other and cover the entire implant 31, so that the implant 31 is stably positioned in the alveolar bone 5 to prevent loosening, thereby increasing the osseointegration effect between the implant 31 and the alveolar bone 5.

Therefore, by utilizing the plurality of interconnected holes 32 or the arrangement of the holes 32 matched with the rough edges 322 in time, the plurality of bone cells BC can be smoothly and rapidly attached to the plurality of edges 322 and the holes 32 to promote the initial climbing and growing capability of the cells BC, and the cells BC can be continuously climbed and rapidly and uniformly distributed in the plurality of channels 323, and the internal communication space of the plurality of channels 323 also enables the implant 31 and the bone cells BC to have a large contact area, which is more beneficial to promoting the attaching and growing capability of the cells, thereby promoting the bone cells BC to generate rapid climbing, proliferating and tight linking actions, not only increasing the bone integration effect after tooth implantation, but also accelerating the healing speed of the bone tissue to shorten the healing time.

In summary, the present invention provides an implant material, wherein a plurality of holes are formed on the surface of the implant, and the edges of the adjacent holes are connected to facilitate the formation of a plurality of channels in series, so that cells derived from the locking site of the implant are smoothly attached to the holes and extend into each channel to rapidly climb, distribute and proliferate, and the proliferated cells are further linked between the holes and the channels, so that the cells climb onto the implant in a short time and cover the implant to be stably positioned, thereby improving the combination effect of the implant and the locking site, not only preventing the implant from loosening, but also increasing the healing speed of the locking site.

The above is only a preferred embodiment of the present invention, and is not intended to limit the present invention, and various modifications and changes will occur to those skilled in the art. Any modification, equivalent replacement, or improvement made within the spirit and principle of the present invention should be included in the protection scope of the present invention.

Claims

1. An implant material is characterized by comprising an implant body with a first end and a second end opposite to the first end; wherein the implant body comprises a drilling locking part and a locking hole which are respectively arranged at the first end and the second end, and a screw thread part which is spirally arranged between the first end and the second end, the surface of the implant is provided with a plurality of holes and comprises a rod body surface which is exposed outwards from the space between any two adjacent screw threads of the screw thread part, each hole is concavely arranged on the surface of the implant and is formed by surrounding a peripheral wall, the peripheral wall is connected with the surface of the implant to form an end edge with non-smooth lines, so that the end edge of each hole is rough, the end edges and the peripheral walls of a plurality of adjacent holes are continuously connected, meanwhile, the space formed between the joint of the adjacent end edge and the peripheral wall positioned on the same side and the joint of the adjacent end edge and the peripheral wall positioned on the other opposite side is communicated with the outside, so that the plurality of adjacent holes are communicated in series to form a pair of externally communicated channels, and the plurality of adjacent holes in series are communicated to form a plurality of channels.

2. The implant of claim 1, wherein the implant surface further comprises a thread surface of the thread portion.

3. The implant material as claimed in any one of claims 1 to 2, wherein the thread portion comprises at least two thread segments, a thread pitch is formed between any two adjacent threads of the plurality of thread segments, and the thread pitches of the plurality of thread segments are different.

4. The implant of claim 3, wherein the second end has a maximum outer diameter greater than a maximum outer diameter of the first end.

5. The implant of claim 1, wherein the ends of the plurality of holes are connected in a lateral direction to form separate channels extending laterally therethrough.

6. The implant of claim 1, wherein the ends of the plurality of holes are connected in a longitudinal direction to form separate channels extending longitudinally therethrough.

7. The implant of claim 1, wherein the ends of the holes are connected in a transverse and longitudinal direction, such that the adjacent channels are connected to each other to form a criss-cross through pattern.